Localization system and method useful in the acquisition and analysis of cardiac information

ABSTRACT

Provided are a localization system and method useful in the acquisition and analysis of cardiac information. The localization system and method can be used with systems that perform cardiac mapping, diagnosis and treatment of cardiac abnormalities, as examples, and in the retrieval, processing, and interpretation of such types of information. The localization system and method use high impedance inputs, improved isolation, and relatively high drive currents for pairs of electrodes used to establish a multi-axis coordinate system. The axes can be rotated and scaled to improve localization.

RELATED APPLICATIONS

The present application claims priority under 35 USC 119(e) to U.S. Provisional Patent Application Ser. No. 62/161,213, entitled “Localization System and Method Useful in the Acquisition and Analysis of Cardiac Information”, filed May 13, 2015, which is incorporated herein by reference in its entirety.

The present application, while not claiming priority to, may be related to U.S. patent application Ser. No. 14/865,435, entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, filed Sep. 25, 2015, which is a continuation of U.S. Pat. No. 9,167,982 (hereinafter the '982 patent), entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, issued Oct. 27, 2015, which is a continuation of U.S. Pat. No. 8,918,158 (hereinafter the '158 patent), entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, issued Dec. 23, 2014, which is a continuation of U.S. Pat. No. 8,700,119 (hereinafter the '119 patent), entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, issued Apr. 15, 2014, which is a continuation of U.S. Pat. No. 8,417,313 (hereinafter the '313 patent), entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, issued Apr. 9, 2013, which was a 35 USC 371 national stage filing of Patent Cooperation Treaty Application No. CH2007/000380, entitled “Method and Device for Determining and Presenting Surface Charge and Dipole Densities on Cardiac Walls”, filed Aug. 3, 2007, published as WO 2008/014629, which claimed priority to Swiss Patent Application No. 1251/06 filed Aug. 3, 2006, each of which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to U.S. patent application Ser. No. 14/886,449, entitled “Device and Method For the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, filed Oct. 19, 2015, which is a continuation of U.S. Pat. No. 9,192,318 (hereinafter the '318 patent), entitled “Device and Method For the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, issued Nov. 24, 2015, which is a continuation of U.S. Pat. No. 8,512,255, entitled “Device and Method for the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, issued Aug. 20, 2013, published as US2010/0298690 (hereinafter the '690 publication), which was a 35 USC 371 national stage application of Patent Cooperation Treaty Application No. PCT/IB09/00071 filed Jan. 16, 2009, entitled “A Device and Method for the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, published as WO2009/090547, which claimed priority to Swiss Patent Application 00068/08 filed Jan. 17, 2008, each of which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to U.S. application Ser. No. 14/003,671, entitled “Device and Method for the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, filed Sep. 6, 2013, which is a 35 USC 371 national stage filing of Patent Cooperation Treaty Application No. PCT/US2012/028593, entitled “Device and Method for the Geometric Determination of Electrical Dipole Densities on the Cardiac Wall”, published as WO2012/122517 (hereinafter the '517 publication), which claimed priority to U.S. Patent Provisional Application Ser. No. 61/451,357, each of which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to U.S. Design application Ser. No. 29/475,273, entitled “Catheter System and Methods of Medical Uses of Same, Including Diagnostic and Treatment Uses for the Heart”, filed Dec. 2, 2013, which is a 35 USC 371 national stage filing of Patent Cooperation Treaty Application No. PCT/US2013/057579, entitled “Catheter System and Methods of Medical Uses of Same, Including Diagnostic and Treatment Uses for the Heart”, filed Aug. 30, 2013, which claims priority to U.S. Patent Provisional Application Ser. No. 61/695,535, entitled “System and Method for Diagnosing and Treating Heart Tissue”, filed Aug. 31, 2012, which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to U.S. application Ser. No. 14/762,944, entitled “Expandable Catheter Assembly with Flexible Printed Circuit Board (PCB) Electrical Pathways”, filed Jul. 23, 2015, which is a 35 USC 371 national stage filing of Patent Cooperation Treaty Application No. PCT/US2014/15261, entitled “Expandable Catheter Assembly with Flexible Printed Circuit Board (PCB) Electrical Pathways”, filed Feb. 7, 2014, published as WO2014/124231, which claims priority to U.S. Patent Provisional Application Ser. No. 61/762,363, entitled “Expandable Catheter Assembly with Flexible Printed Circuit Board (PCB) Electrical Pathways”, filed Feb. 8, 2013, which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to Patent Cooperation Treaty Application No. PCT/US2015/11312, entitled “Gas-Elimination Patient Access Device”, filed Jan. 14, 2015, which claims priority to U.S. Patent Provisional Application Ser. No. 61/928,704, entitled “Gas-Elimination Patient Access Device”, filed Jan. 17, 2014, which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to Patent Cooperation Treaty Application No. PCT/US2015/22187, entitled “Cardiac Analysis User Interface System and Method”, filed Mar. 24, 2015, which claims priority to U.S. Patent Provisional Application Ser. No. 61/970,027, entitled “Cardiac Analysis User Interface System and Method”, filed Mar. 28, 2014, which is hereby incorporated by reference.

The present application, while not claiming priority to, may be related to U.S. application Ser. No. 14/916,056, entitled “Devices and Methods for Determination of Electrical Dipole Densities on a Cardiac Surface”, filed Mar. 2, 2016, which is a 35 USC 371 national stage filing of Patent Cooperation Treaty Application No. PCT/US2014/54942, entitled “Devices and Methods for Determination of Electrical Dipole Densities on a Cardiac Surface”, filed Sep. 10, 2014, published as WO2015/038607, which claims priority to U.S. Patent Provisional Application Ser. No. 61/877,617, entitled “Devices and Methods for Determination of Electrical Dipole Densities on a Cardiac Surface”, filed Sep. 13, 2013, which is hereby incorporated by reference.

FIELD

The present invention is generally related to systems and methods that may be useful for the diagnosis and treatment of cardiac arrhythmias or other abnormalities, in particular, the present invention is related to systems, devices, and methods useful in performing localization of such arrhythmias or other abnormalities.

BACKGROUND

For localizing the origin(s) of cardiac arrhythmias it is common practice to measure the electric potentials located on the inner surface of the heart by electrophysiological means within the patient's heart. One method is to insert electrode catheters into the heart to record cardiac potentials during normal heart rhythm or cardiac arrhythmia. If the arrhythmia has a regular activation sequence, the timing of the electric activation measured in voltages at the site of the electrode can be accumulated when moving the electrode around during the arrhythmia, to create a three-dimensional map of the electric activation. By doing this, information on the localization of the source of arrhythmia(s) and mechanisms, i.e., re-entry circuits, can be diagnosed to initiate or guide treatment (radiofrequency ablation). The information can also be used to guide the treatment of cardiac resynchronization, in which implantable pacing electrodes are placed in specific locations within the heart wall or chambers to re-establish a normal level of coordinated activation of the heart.

A method using external sensors measures the electrical activity of the heart from the body surface using electrocardiographic techniques that include, for example, electrocardiograms (ECG) and vectorcardiography (VCG). These external sensor techniques can be limited in their ability to provide information and/or data on regional electrocardiac activity. These methods can also fail to localize bioelectric events in the heart.

A method using external sensors for the localization of cardiac arrhythmias utilizes body surface mapping. In this technique, multiple electrodes are attached to the entire surface of the thorax and the information of the cardiac electrograms (surface ECG) is measured in voltages that are accumulated into maps of cardiac activation. This measurement can be problematic because the electrical activity is time dependent and spatially distributed throughout the myocardium and also fails to localize bioelectric events in the heart. Complex mathematical methods are required to determine the electric activation upon the outer surface of a heart model (i.e. epicardium), for instance, one obtained from CT or MRI imaging giving information on cardiac size and orientation within the thoracic cavity.

Alternatively, recordings of potentials at locations on the torso, for example, can provide body surface potential maps (BSPMs) over the torso surface. Although the BSPMs can indicate regional cardiac electrical activity in a manner that can be different from conventional ECG techniques, these BSPM techniques generally provide a comparatively low resolution, smoothed projection of cardiac electrical activity that does not facilitate visual detection or identification of cardiac event locations (e.g., sites of initiation of cardiac arrhythmias) and/or details of regional activity (e.g., number and location of arrythmogenic foci in the heart).

Since the localization of cardiac arrhythmias by the use of potentials is imprecise, the successful treatment of cardiac arrhythmias has been difficult and has demonstrated limited success and reliability. There is, therefore, a need for improved methods of localizing, diagnosing and treating cardiac arrhythmias.

SUMMARY

In accordance with an aspect of the inventive concept, provided is a localization system, comprising: at least one catheter configured for delivery of one or more biopotential electrodes to a body cavity defined by surrounding tissue; a patient interface module comprising a plurality of localization electrodes configured for fixed orientation relative to the body; a cardiac information console configured to process localization signals from the localization electrodes to establish a manipulatable coordinate system for the tissue and to process the biopotential signals to orient the biopotential electrodes within the coordinate system.

In various embodiments, the cavity is a heart chamber and the surrounding tissue is one or more walls of the heart chamber.

In various embodiments, the one or more biopotential electrodes is a plurality of biopotential electrodes coupled to a distal end of the at least one catheter.

In various embodiments, the biopotential electrodes are disposed on a 3D array.

In various embodiments, the 3D array includes a plurality of splines.

In various embodiments, the 3D array is a basket array, a spiral array, a balloon, radially deployable arms, and/or other expandable and compactible structures.

In various embodiments, the patient interface module includes a patient isolation drive system, a set of patch electrodes, and one or more reference electrodes.

In various embodiments, the localization electrodes include one or more pairs of localization electrodes.

In various embodiments, the localization electrodes include two pairs of localization electrodes.

In various embodiments, each pair of localization electrodes defines an axis of the coordinate system.

In various embodiments, the localization electrodes include three pairs of localization electrodes, each pair of localization electrodes defining one axis of the coordinate system.

In various embodiments, a first pair of localization electrodes has two patch electrodes placed on opposite sides of the ribs; a second pair of localization electrodes has one patch electrode placed on the lower back and one patch electrode placed on the upper chest; and a third pair of localization electrodes has one patch electrode placed on the upper back and one patch electrode placed on the lower abdomen.

In various embodiments, the axes are non-orthogonal to a natural axis of the body.

In various embodiments, the pairs of localization electrodes are placed such that the axes intersect at an origin, and the origin is located in the heart.

In various embodiments, the origin of the three intersecting axes is centered on an atrial volume.

In various embodiments, the isolation drive system is configured to isolate the localization signals from the cardiac information console to prevent current leakage.

In various embodiments, the isolation drive system is configured to maintain simultaneous output on all axes generated by the localization electrode pairs.

In various embodiments, each pair of localization electrodes is driven by a different localization signal.

In various embodiments, each localization signal has a different frequency.

In various embodiments, the signals generated for the first pair of electrodes has a frequency of about 39 kHz; the signals generated for the second pair of electrodes has a frequency of about 48 kHz; and the signals generated for the third pair of electrodes has a frequency of about 52 kHz.

In various embodiments, the cardiac information console is further configured to rotate the coordinate system to adjust and correct an electronic representation of the 3D array of biopotentials.

In various embodiments, the cardiac information console is further configured to scale the coordinate system to adjust and correct an electronic representation of the 3D array of biopotentials.

In various embodiments, the cardiac information console is further configured to fit an electronic representation of the 3D array of biopotentials to a known or determined geometry of the 3D array of biopotentials.

In various embodiments, the system further comprises a user interface system configured to display the 3D array of biopotential electrodes and the coordinate system.

In various embodiments, the user interface system includes a mechanism that enables a user to rotate and/or scale the coordinate system to graphically adjust and correct an image of the 3D array of biopotentials.

In various embodiments, the cardiac information console further comprises, for each electrode, a biopotential signal path having a high impedance input and configured to receive biopotential signals from the biopotential electrodes; and/or a localization signal path having a high impedance input and configured to receive localization signals from the localization electrodes.

In various embodiments, the cardiac information console further comprises, for each electrode, a DFIB protection circuit coupled between the biopotential signal path and the localization signal path.

In various embodiments, the cardiac information console further comprises, for each electrode, an ADC coupled to outputs of the biopotential signal path and the localization signal path.

In various embodiments, the cardiac information console further comprises, coupled to an ADC output, a biopotential signal processor configured to provide cardiac activity mapping from processed biopotential data and a localization signal processor configured to localize the biopotential electrodes.

In various embodiments, the system further comprises an IQ demodulator, for each electrode, coupled to the output of the ADC and configured to separate the magnitude and phase of a received data signal; a narrow band IIR filter coupled to the IQ demodulator, and a time filter coupled to the IIR filter, and configured to selectively filter out portions of data on a time basis.

In various embodiments, there is one IIR filter, comprising an I portion and a Q portion, for each IQ demodulator.

In various embodiments, there is one multichannel IIR filter for a plurality of IQ demodulators.

In various embodiments, the system further comprises one or more auxiliary catheters.

In various embodiments, the one or more auxiliary catheters comprises at least one of an ablation catheter or a reference catheter.

In various embodiments, the at least one catheter further includes ultrasound electrodes configured to collect image data to generate one or more images of the tissue.

In various embodiments, the cardiac information console further comprises an ultrasound signal path having a high impedance input and configured to receive ultrasound signals from the ultrasound electrodes.

In various embodiments, the system comprises one or more sensors configured to produce one or more signals indicating a presence of, an absence of, and/or a change in at least one sensed condition.

In various embodiments, the one or more sensors comprises at least one catheter sensor.

In various embodiments, the at least one catheter sensor comprises a sensor mounted to or integral with: a catheter handle of the at least one catheter and/or a catheter array coupled to a distal end of the at least one catheter.

In various embodiments, the at least one catheter sensor comprises a patient physiologic sensor selected from the group consisting of: a blood pressure sensor; a blood gas sensor; a temperature sensor; a blood glucose sensor; a pH sensor; a respiration sensor; an average clotting time (ACT) sensor; and combinations of one or more of these.

In various embodiments, the one or more sensors comprises at least one cardiac information console sensor.

In various embodiments, the one or more sensors comprises at least one patient interlace system sensor.

In various embodiments, the one or more sensors comprises a plurality of sensors, including at least two sensors selected from the group consisting of: a catheter sensor; a cardiac information console sensor; a patient interface system sensor; and combinations of one or more these.

In various embodiments, the one or more sensors comprise at least one sensor selected from the group consisting of: a force sensor; a pressure sensor; a strain gauge; an optical sensor; an imaging sensor; a sound sensor; a hall effect sensor; a pH sensor; a magnetic sensor; a temperature sensor; and combinations of one or more of these.

In various embodiments, the imaging sensor includes a lens and/or optical fiber.

In various embodiments, the sound sensor includes a ultrasound sensor.

In various embodiments, the one or more of sensors comprise at least one transducer selected from the group consisting of: a heating element; a cooling element; a vibrating element; a drug or other agent delivery element; a magnetic field generating element; a light delivery element; an imaging element; and combinations of one or more of these.

In various embodiments, the imaging element includes a lens and/or optical fiber.

In various embodiments, the system is configured to analyze the one or more signals produced by the one or more sensors.

In various embodiments, the system is configured to perform an analysis of one or more signals produced by the one or more of sensors in combination with voltage data, dipole density data, surface charge data, and/or anatomical data sensed and/or calculated by the system.

In various embodiments, the one or more signals from the one or more sensors are used by system to perform a function selected from the group consisting of: improve an anatomical image displayed by system; improve cardiac information displayed by system (e.g. dipole density and/or surface charge information); detect a malfunction of system; provide physiologic data of a patient; and combinations of one or more of these.

In various embodiments, the cardiac information displayed by system includes at least one of dipole density information and/or surface charge information.

In accordance with another aspect of the inventive concept, provided is a localization method, comprising: delivering one or more biopotential electrodes to a body cavity defined by surrounding tissue using at least one catheter; receiving biopotential signals from the one or more biopotential electrodes; establishing a manipulatable coordinate system for the tissue using localization electrodes having a fixed orientation relative to the body; and processing the biopotential signals to orient and/or reorient the biopotential electrodes within the coordinate system.

In various embodiments, the cavity is a heart chamber and the surrounding tissue is one or more walls of the heart chamber.

In various embodiments, the one or more biopotential electrodes is a plurality of biopotential electrodes coupled to a distal end of the at least one catheter.

In various embodiments, the biopotential electrodes are disposed on a 3D array.

In various embodiments, the 3D array includes a plurality of splines.

In various embodiments, the 3D array is a basket array, spiral array, a balloon, radially deployable arms, and/or other expandable and compactible structures.

In various embodiments, the localization electrodes include a set of patch electrodes and one or more reference electrodes.

In various embodiments, the localization electrodes include one or more pairs of localization electrodes.

In various embodiments, the localization electrodes include two pairs of localization electrodes.

In various embodiments, each pair of localization electrodes defines an axis of the coordinate system.

In various embodiments, the localization electrodes include three pairs of localization electrodes, each pair of localization electrodes defining one axis of the coordinate system.

In various embodiments, a first pair of localization electrodes has two patch electrodes placed on opposite sides of the ribs, a second pair of localization electrodes has one patch electrode placed on the lower back and one patch electrode placed on the upper chest, and a third pair of localization electrodes has one patch electrode placed on the upper back and one patch electrode placed on the lower abdomen.

In various embodiments, the axes are non-orthogonal to a natural axis of the body.

In various embodiments, the pairs of localization electrodes are placed such that the axes intersect at an origin, and the origin is located in the heart.

In various embodiments, the origin of the three intersecting axes is centered on an atrial volume.

In various embodiments, the method further comprises maintaining simultaneous output on all axes generated by the localization electrode pairs.

In various embodiments, the method further comprises driving each pair of localization electrodes with a different localization signal.

In various embodiments, each localization signal has a different frequency.

In various embodiments, the method further comprises generating the signals for the first pair of electrodes at a frequency of about 39 kHz; generating the signals for the second pair of electrodes at a frequency of about 48 kHz; and generating the signals for the third pair of electrodes at a frequency of about 52 kHz.

In various embodiments, receiving biopotential signals from the one or more biopotential electrodes includes: using at least one processor, rotating the coordinate system to adjust and correct an electronic representation of a 3D array of biopotentials sensed and/or recorded by the one or more biopotential electrodes.

In various embodiments, the method further comprises using at least one processor, scaling the coordinate system to adjust and correct an electronic representation of the 3D array of biopotentials.

In various embodiments, the method further comprises fitting an electronic representation of the 3D array of biopotentials to a known or determined geometry of the 3D array of biopotentials.

In various embodiments, the method further comprises displaying the 3D array of biopotential electrodes and the coordinate system on at least one display of a user interface system.

In various embodiments, the method further comprises rotating and/or scaling the coordinate system to graphically adjust and correct an image of the 3D array of biopotentials in response to user interaction with the user interface system.

In various embodiments, processing the biopotential signals includes: receiving I and Q data based on the receiving biopotential signals; converting the IQ data to voltage data; applying an axis correction factor to the voltage data, based on a known and/or measured shape of the electrode array; determining a scaling matrix and applying the scaling matrix to the sensed voltage data, based on a known and/or measured shape of the electrode array; calculating position values of each electrode, each electrode having a corrected voltage value based on the axis correction and scaling of the voltage data; and fitting the calculated position values of each electrode to a known basket configuration.

In various embodiments, the method further comprises applying fitting and rotations to the calculated electrode positions; and updating the electrode positions.

In various embodiments, the method further comprises, if a next set of biopotential data exists, repeating the method for the next set of biopotential data.

In various embodiments, the localization electrodes include a plurality of pairs of localization electrodes and there are is one axis for each pair of localization electrodes, and the method comprises rotating, scaling and/or deskewing one or more of the axes until the electrode array takes a predetermined shape.

In various embodiments, the electrode array is a 3D basket array.

In various embodiments, the method further comprises displaying the electrode array on a display of a user interface subsystem.

In various embodiments, applying the scaling matrix comprises, if a length or a size of the electrode array is incorrect, based on known or determined proportions of the electrode array, scaling one or more of the axes of the electrode array longer or shorter until the known or determined proportions of the electrode array is/are achieved.

In various embodiments, the method further comprises, for each electrode: receiving biopotential signals from the biopotential electrodes via a biopotential signal path having a high impedance input; and/or receiving localization signals from the localization electrodes via a localization signal path having a high impedance input.

In various embodiments, the method further comprises, for each electrode: coupling a DFIB protection circuit between the biopotential signal path and the localization signal path.

In various embodiments, the method further comprises, for each electrode: coupling outputs of the biopotential signal path and the localization signal path to an ADC.

In various embodiments, the method further comprises coupling a biopotential signal processor and a localization signal processor to an ADC output; providing cardiac activity mapping from processed biopotential data using the biopotential signal processor; and localizing the biopotential electrodes using the localization signal processor.

In various embodiments, the method further comprises for each electrode, coupling an IQ demodulator to the output of the ADC and separating a magnitude and a phase of a received biopotential signals; coupling a narrow band IIR filter to the IQ demodulator; and coupling a time filter to the IIR filter, and selectively filtering out portions of data on a time basis.

In various embodiments, there is one IIR filter, comprising an I portion and a Q portion, for each IQ demodulator.

In various embodiments, there is one multichannel IIR filter for a plurality of IQ demodulators.

In various embodiments, the method further comprises delivering one or more auxiliary catheters to the body cavity.

In various embodiments, the one or more auxiliary catheters comprises at least one of an ablation catheter or a reference catheter.

In various embodiments, the at least one catheter further includes ultrasound electrodes, and the method includes collecting image data from the ultrasound electrodes to generate an image of the tissue.

In various embodiments, the method further comprises receiving ultrasound signals from the ultrasound electrodes via an ultrasound signal path having a high impedance input.

In accordance with aspects of the inventive concept, provided is a localization method as shown and/or described.

In accordance with aspects of the inventive concept, provided is a localization system as shown and/or described.

In accordance with aspects of the inventive concept, provided is a cardiac information processing system as shown and/or described.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 provides a block diagram of an embodiment of a cardiac information processing system, in accordance with aspects of the inventive concept.

FIG. 2 provides a circuit diagram of an embodiment of the localization driving circuitry and UI system of FIG. 1.

FIG. 3 is a drawing providing a front view and a back view of a patient and relative electrode placement, in accordance with aspects of the inventive concept.

FIG. 4 provides a block diagram of another embodiment of a cardiac information processing system, in accordance with aspects of the inventive concept.

FIG. 5 provides a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, in accordance with aspects of the inventive concept.

FIG. 6 is a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, as one implementation of the approach of FIG. 5, in accordance with aspects of the inventive concept.

FIG. 7 is a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, as another implementation of the approach of FIG. 5, in accordance with aspects of the inventive concept.

FIG. 8 is an embodiment of a localization method, in accordance with aspects of the inventive concepts.

FIG. 9 is a schematic diagram of an ablation catheter, in accordance with aspects of the inventive concept.

FIG. 10 is a schematic diagram of an ultrasound high input impedance switch, in accordance with aspects of the inventive concept.

DETAILED DESCRIPTION

Various exemplary embodiments will be described more fully hereinafter with reference to the accompanying drawings, in which some exemplary embodiments are shown. The present inventive concept can, however, be embodied in many different forms and should not be construed as limited to the exemplary embodiments set forth herein.

It will be understood that, although the terms first, second, etc. are used herein to describe various elements, these elements should not be limited by these terms. These terms are used to distinguish one element from another, but not to imply a required sequence of elements. For example, a first element can be termed a second element, and, similarly, a second element can be termed a first element, without departing from the scope of the present invention. As used herein, the term “and/or” includes any and all combinations of one or more of the associated listed items. And a “combination” of associated listed items need not include all of the items listed, but can include all of the items listed.

It will be understood that when an element is referred to as being “on” or “attached”, “connected” or “coupled” to another element, it can be directly on or connected or coupled to the other element or intervening elements can be present. In contrast, when an element is referred to as being “directly on” or “directly connected” or “directly coupled” to another element, there are no intervening elements present. Other words used to describe the relationship between elements should be interpreted in a like fashion (e.g., “between” versus “directly between,” “adjacent” versus “directly adjacent,” etc.).

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the singular forms “a,” “an” and “the” are intended to include the plural forms as well, unless the context clearly indicates otherwise. It will be further understood that the terms “comprises,” “comprising,” “includes” and/or “including,” when used herein, specify the presence of stated features, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, steps, operations, elements, components, and/or groups thereof.

Spatially relative terms, such as “beneath,” “below,” “lower,” “above,” “upper” and the like can be used to describe an element and/or feature's relationship to another element(s) and/or feature(s) as, for example, illustrated in the figures. It will be understood that the spatially relative terms are intended to encompass different orientations of the device in use and/or operation in addition to the orientation depicted in the figures. For example, if the device in the figures is turned over, elements described as “below” and/or “beneath” other elements or features would then be oriented “above” the other elements or features. The device can be otherwise oriented (e.g., rotated 90 degrees or at other orientations) and the spatially relative descriptors used herein interpreted accordingly.

Various exemplary embodiments are described herein with reference illustrations of idealized or representative structures and intermediate structures. As such, variations from the shapes of the illustrations as a result, for example, of manufacturing techniques and/or tolerances, are to be expected. Thus, exemplary embodiments should not be construed as limited to the particular shapes of regions illustrated herein but are to include deviations in shapes that result, for example, from manufacturing.

To the extent that functional features, operations, and/or steps are described herein, or otherwise understood to be included within various embodiments of the inventive concept, such functional features, operations, and/or steps can be embodied in functional blocks, units, modules, operations and/or methods. And to the extent that such functional blocks, units, modules, operations and/or methods include computer program code, such computer program code can be stored in a computer readable medium, e.g., such as non-transitory memory and media, that is executable by at least one computer processor.

Referring now to FIG. 1, provided is a block diagram of an embodiment of a cardiac information processing system 100, in accordance with aspects of the inventive concept. The cardiac information processing system 100 can be or include a system configured to perform cardiac mapping, diagnosis, and/or treatment, such as for treating abnormalities such as arrhythmia. Additionally or alternatively, the system can be a system configured for teaching and or validating devices and methods of diagnosing and/or treating cardiac abnormalities or disease of a patient P.

The cardiac information processing system 100 includes a catheter 10, a cardiac information console 20, and a patient interface module 50 that can be configured to cooperate to accomplish the various functions of the cardiac information processing system 100. Preferably, cardiac information processing system 100 includes a single power supply (PWR), which can be shared by the cardiac information console 20 and the patient interface module 50. Unlike typical systems, use of a single power supply in this way can greatly reduce the chance for leakage currents to propagate into the patient interface module 50 and cause errors in localization.

The catheter 10 includes an electrode array 12 that can be percutaneously delivered to a heart chamber (HC). The array of electrodes has a known spatial configuration. For example, in the expanded state the physical relationship of the electrodes can be known or reliably assumed. Diagnostic catheter 10 also includes a handle 14, and an elongate flexible shaft 16 extending from handle 14. Attached to the distal end of shaft 16 is the electrode array 12, such as a 3D array in the form of a radially expandable and/or compactible assembly. In this embodiment, the electrode array 12 is shown as a basket array, but the electrode array could take other forms in other embodiments. In some embodiments, expandable electrode array 12 is constructed and arranged as described in reference to applicant's co-pending Patent Cooperation Treaty Patent Application Serial Number PCT/US2013/057579, titled “System and Method for Diagnosing and Treating Heart Tissue”, filed Aug. 30, 2013, the content of which is incorporated herein by reference by its entirety. In other embodiments, expandable electrode array 12, as a 3D array, can comprise a balloon, radially deployable arms, spiral, and/or other expandable and compactible structure.

Shaft 16 and expandable electrode array 12 are constructed and arranged to be inserted into a body (e.g. an animal body or a human body, such as the body of Patient P), and advanced through a body vessel, such as a femoral vein or other blood vessel. Shaft 16 and electrode array 12 can be constructed and arranged to be inserted through an introducer (not shown), such as when electrode array 12 is in a compacted state, and slidingly advanced through a lumen of a shaft into a body space, such as a chamber of the heart (HC), such as the right atrium or the left atrium, as examples.

Expandable electrode array 12 can further comprise multiple splines, each spline having a plurality of electrodes 12 a. Three splines are visible in FIG. 1, but the basket array is not limited to three splines; more or less splines can be included in the basket array. Each electrode 12 a can be configured to record a voltage, such as the voltage present on a surface of the heart or at a location within a heart chamber HC. As a non-limiting example, the three electrodes 12 a are shown on each spline in this embodiment. However, in other embodiments the basket array can include more or less electrodes.

Catheter 10 can comprise a cable or other conduit, such as cable 18, configured to electrically, optically, and/or electro-optically connect catheter 10 to the cardiac information console 20 via connectors 18 a and 20 a, respectively.

The patient interface module 50 can be configured to electrically isolate one or more components of the cardiac information console 20 from patient P (e.g., to prevent undesired delivery of a shock or other undesired electrical energy to patient P). The patient interface module 50 can be integral with cardiac information console 20 and/or it can comprise a separate discrete component (e.g. separate housing), as is shown. The cardiac information console 20 comprises one or more connectors 20 b, each comprising a jack, plug, terminal, port, or other custom or standard electrical, optical, or electro-optical connector. Similarly, the patient interface module 50 includes one or more connectors 50 b. At least one cable 52 connects the patient interface module 50 with the cardiac information console 20, via connectors 20 b and 50 b.

The patient interface module 50 includes a patient isolation drive system 54 and a set of localization electrodes. In this embodiment, the set of localization electrodes includes a set of patch electrodes 56 and one or more reference electrode 58. The isolation drive system 54 isolates localization signals from the rest of system to prevent current leakage, e.g., signal loss—resulting in performance degradation. The isolation drive system 54 can minimize drift in localization positions and maintain a high isolation between axes. Additionally, the isolation drive system 54 maintains simultaneous output on all axes, while also increasing the sampling rate at each electrode position. In some embodiments, the sampling rate comprises a rate between 10 kHz and 1 MHz, such as a sampling rate of approximately 625 kHz.

In this embodiment, the set of patch electrodes 56 include three (3) pairs of patch electrodes: an “X” pair having two patch electrodes placed on opposite sides of the ribs (X1, X2); a pair having one patch electrode placed on the lower back (Z1) and one patch electrode placed on the upper chest (Z2); and a “Y” pair having one patch electrode placed on the upper back (Y1) and one patch electrode placed on the lower abdomen (Y2). The patch electrode 56 pairs can be placed on any orthogonal and/or non-orthogonal sets of axes. In the embodiment of FIG. 1, the placement of electrodes is shown on patient P, where electrodes on the back are shown in dashed lines.

The placement of electrodes 56 defines a coordinate system made up of three axes, one axis per pair of patch electrodes 56. In some embodiments, the axes are non-orthogonal to a natural axis of the body: head-to-toe, chest-to-back, and side-to-side (i.e., rib-to-rib). The electrodes can be placed such that the axes intersect at an origin, such as an origin located in the heart. For instance, the origin of the three intersecting axes can be centered in an atrial volume. System 100 can be configured to provide an “electrical zero” that is positioned outside of the heart, such as by locating a reference electrode 58 such that the resultant electrical zero is outside of the heart (e.g. to avoid crossing from a positive voltage to a negative voltage at a location being localized).

Through processing by the cardiac information console 20, the axes can be rotated from the normal physiological orientation, i.e., anterior-posterior, cranial-caudal, left-right. Rotated axes provide improved spatial resolution. Once the desired rotation is achieved, each axis can be scaled, i.e., made longer or shorter, as needed. The rotation and scaling are performed based on comparing expected or known electrode array 12 shape and relative dimensions with a representation of the electrode array in the patch electrode established coordinate system. In such a case, rotation and scaling is performed to bring an incorrect representation into a more accurate representation. Therefore, shaping and scaling the representation of the electrode array 12 serves to adjust and correct the orientation and relative sizes of the axes for far more accurate localization.

The reference electrode(s) 58 can be or include a patch electrode and/or an electrical reference catheter, as a patient reference. A patch electrode can be placed on the skin, and will act as a return for current for defibrillation. An electrical reference catheter can include a unipolar reference electrode used in baseline and restore functions, and can be used for common mode rejection. Another form of electrical reference catheter can be an internal analog reference electrode, which can act as a low noise “analog ground” for all internal catheter electrodes. Each of these types of reference electrodes can be placed in relatively similar locations, such as near lower back in internal vessel (as a catheter) and/or on lower back (as a patch). In some embodiments, system 100 comprises a reference catheter 58 including a fixation mechanism (e.g. a user activated fixation mechanism), which can be constructed and arranged to reduce displacement (e.g. accidental or otherwise unintended movement) of one or more electrodes of the reference catheter 58. The fixation mechanism can comprise a mechanism selected from the group consisting of: spiral expander; spherical expander; circumferential expander; axially actuated expander; rotationally actuated expander; and combinations of two or more of these.

In FIG. 1, aspects of the receiver components of the cardiac information console 20 are depicted. The cardiac information console 20 includes an input defibrillation protection module 22 connected to connector 20 a, which is configured to receive cardiac information from the catheter 10. The DFIB protection module 22 is configured to have a precise clamping voltage and a minimum capacitance. Functionally, the DFIB protection module 22 acts a surge protector.

The DFIB protection module 22 is coupled to two signal paths, a biopotential (BIO) signal path 30 and a localization (LOC) signal path 40. Generally, the BIO path 30 filters noise and preserves the measured biopotential data, and also enables the biopotential signals to be read while ablating, which is not the case in other systems. Generally, the LOC path 40 allows high voltage inputs, while filtering noise from received localization data.

The BIO signal path 30 includes an RF filter 31 coupled to the DFIB protection module 22. In this embodiment, the RF filter 31 operates as a low-pass filter having a high input impedance. The high input impedance is preferred in this embodiment because it minimizes the loss of voltage from the source, e.g., catheter 10, thereby better preserving the received signals. The RF filter 31 is configured to allow biopotential signals from the electrodes 12 a on catheter 10 to pass, e.g., frequencies less than 500 Hz, such as frequencies in the range of 0.1 Hz to 500 Hz. However, high voltages, such as from ablation, are filtered out from the biopotential signal path 30. RF filter 31 can comprise a bandwidth between 10 kHz and 12 kHz.

A BIO amplifier 32 is preferably a low noise single-ended input amplifier that amplifies the RF filtered signal. A BIO filter 33 filters noise out of the amplified signal. BIO filter 33 can comprise an approximately 3 kHz filter. In some embodiments, BIO filter 33 comprises an approximately 7.5 kHz filter, such as when system 100 is configured to accommodate pacing of the heart (e.g. avoid significant signal loss and/or degradation during pacing of the heart).

The LOC signal path 40 includes a high voltage buffer 41 coupled to the DFIB protection module 22. In this embodiment, the high voltage buffer 41 is configured to accommodate the relatively high RF voltages used in treatment techniques, such as RF ablation. For example, the high voltage buffer can have ±100 voltage rails. The high voltage buffer 41 also has a high input impedance, such as when the high voltage buffer 41 does not include a pre-filter stage, and has good performance at high frequencies. A high frequency bandpass filter 42 is coupled to the high voltage buffer 41, and has a passband frequency range of about 20 kHz to 80 kHz for use in localization. Preferably, the filter 42 has low noise with good gain, e.g., a gain of 1.

An AD (analog-to-digital) converter ADC 24 is coupled to the BIO filter 33 of the BIO signal path 30 and to the high frequency filter 42 of the LOC signal path 40. The ADC 24 has high oversampling to allow noise shaping and filtering, e.g., with an oversampling rate of about 625 kHz. In some embodiments, sampling is performed at or above the Nyquist frequency of system 100. The ADC 24 is a multi-channel circuit that can combine BIO and LOC signals or keep them separate. In one embodiment, as a multi-channel circuit, the ADC 24 can be configured to accommodate 48 biopotential electrodes 12 a and 32 auxiliary electrodes (e.g., for ablation or other processes), for a total of 80 channels. In other embodiments, more or less channels can be provided. In FIG. 1, for example, almost all of the elements of the cardiac information console 20 can be duplicated for each channel, e.g., except for the UI system 27. For example, the cardiac information console 20 can include a separate ADC for each channel, or an 80 channel ADC.

Consistent with the two different signals and signal paths 30, 40, signal information from each path is input to and output from the various channels of the ADC 24. Outputs from the channels of the ADC 24 are coupled to either the BIO signal processing module 34 or the LOC signal processing module 44, which pre-process their respective signals for subsequent processing as described herein below. In each case, the preprocessing prepares the received signals for the processing by their respective dedicated processors discussed below. The BIO signal processing module 34 and the LOC signal processing module 44 can be implemented in firmware, in whole or in part, in some embodiments.

The biopotential signal processing module 34 can provide gain and offset adjustment and digital RF filtering having a non-dispersive low pass filter and intermediate frequency band. The intermediate frequency band can eliminate ablation and localization signals. Additionally, the biopotential signal processing can also include pace blanking, which is the blanking of received information during a timeframe when, for example, a physician is “pacing” the heart. Cardiac pacing is applied clinically by standard means. The pacing may be used to temporarily alter the heart rhythm, trigger the heart beat from specific locations on the cardiac wall, or for checking the health of the cardiac tissue by looking at propagation velocities of the pacing pulses.

To accomplish the foregoing, active and passive pacing trigger and input algorithmic trigger determination can be performed. The algorithmic trigger determination can use subsets of channels, edge detection and/or pulse width detection to determine if pacing has occurred. The biopotential signal processing module 34 can also include digital biopotential filtering, which can be a non-dispersive low pass filter with an optimized output sample rate.

The localization signal processing module 44 can provide individual channel/frequency gain calibration, IQ demodulation with tuned demodulation phase, synchronous and continuous demodulation (no MUXing), narrow band IIR filtering, and time filtering (Interleaving, blanking, etc.), as discussed herein below.

A data processor 26, which may include one or more of a plurality of types of processing circuits (e.g., a microprocessor) and memories, executes computer instructions necessary to perform the processing of the pre-processed signals from the BIO signal processing module 34 and localization signal processing module 44. The data processor 26 can be configured to perform calculations, as well as perform data storage and retrieval, necessary to perform the functions of the cardiac information processing system 100.

In this embodiment, data processor 26 includes a biopotential (Bio) processor 36 and a localization (LOC) processor 46. The biopotential processor 36 can perform processing of measured biopotentials. The LOC processor 46 can perform processing of localization signals.

The biopotential processor 36 can be configured to perform various calculations. For example, the BIO processor 36 can include an enhanced common mode rejection filter, which can be bidirectional to minimize distortion and which may be seeded with a common mode signal. The BIO processor 36 can also include an optimized ultrasound rejection filter and be configured for selectable bandwidth filtering.

The localization processor 46 can be configured to perform various calculations. As discussed in more detail below, the LOC processor 46 can electronically make (calculate) corrections to an axis based on the known shape of electrode array 12, make corrections to scaling of one or more axis based on the known shape of the electrode array 12, and perform “fitting” to align measured electrode positions with known possible configurations, which can be optimized with one or more constraints (e.g. physical constraints such as distance between two electrodes 12 a on a single spline, distance between two electrodes 12 a on two different splines, maximum distance between two electrodes 12 a; minimum distance between two electrodes 12 a, minimum and/or maximum curvature of a spine).

The cardiac information console 20 also includes localization driving circuitry, including a localization signal generator 28 and a localization drive current monitor circuit 29. The localization driving circuitry provides high frequency localization drive signals (e.g., 10 kHz-1 MHz, such as 10 kHz-100 kHz). Localization using drive signals at these high frequencies reduces the cellular response effect on the localization data, e.g., from blood cell deformation, and/or allow higher drive currents, e.g., to achieve a better signal-to-noise ratio. The signal generator 28 produces a high resolution digital synthesis of a drive signal, e.g., sine wave, with ultra-low phase noise timing. The drive current monitoring circuitry provides a high voltage, wide bandwidth current source, which is monitored to measure impedance of the patient P.

The cardiac information console 20 can also include a user interface (UI) subsystem 27 configured to output results of the localization and biopotential processing. The UI subsystem 27 can include at least one display 27 a to graphically render such results in 2D, 3D, or a combination thereof. The user interface system 27 can include one or more mechanisms that enable a user to rotate and/or scale the coordinate system to graphically adjust and correct an image of the 3D array of biopotentials. Such mechanisms can include a touchscreen, mouse, keyboard, light pen, track ball, microphone, and so on.

In some embodiments, system 10 comprises one or more sensors, each configured to produce a signal, a sensor of catheter 10 (e.g. sensor 14 a of handle 14 or sensor 12 c of array 12), a sensor 20 b of cardiac information console 20 and/or a sensor 50 a of patient interface module 50, each as shown in FIG. 1. In some embodiments, system 10 comprises two or more of sensors 12 c, 14 a, 20 b, and/or 50 a. In some embodiments, sensors 12 c, 14 a, 20 b, and/or 50 a comprise a sensor selected from the group consisting of: a force sensor; a pressure sensor; a strain gauge; an optical sensor; an imaging sensor (e.g. a lens or optical fiber); a sound sensor such as an ultrasound sensor; a hall effect sensor; a pH sensor; a magnetic sensor; a temperature sensor; and combinations of one or more of these. In some embodiments, sensor 12 c comprise a patient physiologic sensor, such as a sensor selected from the group consisting of: a blood pressure sensor; a blood gas sensor; a temperature sensor; a blood glucose sensor; a pH sensor; a respiration sensor; an average clotting time (ACT) sensor; and combinations of one or more of these. In some embodiments, system 10 is configured to analyze a signal produced by one, two or more of sensors 12 c, 14 a, 20 b, and/or 50 a. In some embodiments, system 10 (e.g. cardiac information console 20) is configured to perform an analysis of one or more signals produced by one, two or more of sensors 12 c, 14 a, 20 b, and/or 50 a in combination with voltage data, dipole density data, surface charge data, and/or anatomical data (e.g. anatomical data collected by one or more ultrasound transducers 133). In some embodiments, signals from one or more sensors 12 c, 14 a, 20 b, and/or 50 a are used by system 10 to perform a function selected from the group consisting of: improve an anatomical image displayed by system 10; improve cardiac information displayed by system 10 (e.g. dipole density and/or surface charge information); detect a malfunction of system 10; provide physiologic data of a patient; and combinations of one or more of these. In some embodiments, one or more of sensors 12 c, 14 a, 20 b, and/or 50 a can comprise a transducer (e.g. as an alternative to being a sensor or in addition to being a sensor), such as a transducer selected from the group consisting of: a heating element; a cooling element; a vibrating element; a drug or other agent delivery element; a magnetic field generating element; a light delivery element; an imaging element (such as a lens, and/or optical fiber); and combinations of one or more of these.

FIG. 2 provides a circuit diagram of an embodiment of the localization driving circuitry and UI system of FIG. 1. FIG. 2 shows portions of the UI subsystem 27, the localization signal generator 28, and the localization drive current monitor circuit 29 of FIG. 1.

The localization signal generator 28 is a DDS (Direct Digital Synthesizer) that generates waveforms for localization, such as sine waves. One waveform is generated per “axis,” currently a 3 axes system. High frequency sine waves are generated for each axis, such as 3 sine waves at different frequencies. For example, the signals generated for the X pair of electrodes can be at 39 kHz; the signals generated for the Y pair of electrodes can be at 48 kHz; and the signals generated for the Z pair of electrodes can be at 52 kHz.

The drive current monitoring circuitry 29 provides a feedback system for monitoring and maintaining current delivered by the localization system to the patient P, using the ADC as an output. The drive current monitoring circuitry 29 can monitor current output and determine physical parameters of the system, such as impedance of the body, issues with patch placement, changes in physical parameters, and/or hardware error and/or failure.

In this embodiment, the cardiac information console 20 and patient interface module 50 share a common ground, through use of a single power source. As shown, the patient interface module 50 provides localization driver isolation using a transformer. This provides better isolation, while driving different pairs of electrodes, e.g., currently 3 pairs of electrodes are simultaneously driven with 3 different frequencies.

In FIG. 2, the impedance between two electrodes in a pair of electrodes is indicated by “Z” (the customary symbol for impedance).

FIG. 3 is a drawing providing a front view and a back view of a patient and relative electrode placement, in accordance with aspects of the inventive concept. This figure demonstrates a preferred patch electrode placement, as discussed above. In FIG. 1, for example, the X electrodes X1 and X2 are shown as patch electrodes 1 and 2, respectively; the Z electrodes Z1 and Z2 are shown as patch electrodes 3 and 4, respectively; and the Y electrodes Y1 and Y2 are shown as patch electrodes 5 and 6, respectively. Thus, patches 1 and 2 are placed on the ribs, forming X axis within the body; patches 3 and 4 are placed on the lower back and upper chest (respectively), forming the Z axis; and patches 5 and 6 are placed on the upper back and lower abdomen (torso) (respectively), forming the Y Axis. The three axis are of similar length, and not aligned with “natural” axis of the body (i.e., head to toe, chest to back, and side to side).

The reference patch electrode 58 can be placed on the lower back/buttocks. Additionally, or alternatively, a reference catheter can be placed in similar location within a body vessel.

As described hereabove, a patch pair can operate differentially, i.e. neither patch 56 in a pair operates as a reference electrode, and are both driven by system 100 to generate the electrical field between the two. Alternatively or additionally, one or more of the patch electrodes 56 can serve as the reference electrode 58, such that they operate in a single ended mode. One of any pair of patch electrodes 56 can serve as the reference electrode 58 for that patch pair, forming a single-ended patch pair. One or more patch pairs can be configured to be independently single-ended. One or more of the patch pairs can share a patch as a single-ended reference or can have the reference patches of more than one patch pair electrically connected.

Through processing performed by the cardiac information console 20, the axes can be transformed, e.g., rotated, from a first orientation, e.g., a non-physiological orientation based on the placement of electrodes 56, to a second orientation. The second orientation can comprise a standard Left-Posterior-Superior (LPS) anatomical orientation, i.e., the “x” axis is oriented from right to left of the patient, the “y” axis is oriented from the anterior to posterior of the patient, and the “z” axis is oriented from cauda to cranial of the patient. Placement of patch electrodes 56 and the non-standard axes defined thereby can be selected to provide improved spatial resolution when compared to patch electrode placement resulting in a normal physiological orientation of the resulting axes, e.g. due to preferred tissue characteristics between electrodes 56 in the non-standard orientation. For example, non-standard electrode placement can result in diminished influence of the low-impedance volume of the lungs on the localization field. Furthermore, electrode placement can be selected to create axes which pass through the body of the patient along paths of similar or equivalent lengths. Axes of similar length will possess more similar energy density per unit distance within the body, yielding a more uniform spatial resolution along such axes. Transforming the non-standard axes into a standard orientation can provide a more straightforward display environment for the user. Once the desired rotation is achieved, each axis can be scaled, i.e., made longer or shorter, as needed. The rotation and scaling are performed based on comparing pre-determined, e.g., expected or known, electrode array 12 shape and relative dimensions, with measured values that correspond to the shape and relative dimensions of the electrode array in the patch electrode established coordinate system. For example, rotation and scaling can be performed to transform a relatively inaccurate, e.g., uncalibrated, representation into a more accurate representation. Shaping and scaling the representation of the electrode array 12 can adjust, align, and/or otherwise improve the orientation and relative sizes of the axes for far more accurate localization.

The reference electrode(s) 58 can be or include a patch electrode and/or an electrical reference catheter, as a patient reference. A patch electrode 58 can be placed on the skin, and will act as a return for current for defibrillation. An electrical reference catheter can include a unipolar reference electrode used to enhance common mode rejection. The unipolar reference electrode, or other electrodes on a reference catheter, can be used to measure, track, correct, or calibrate physiological, mechanical, electrical, or computational artifacts in a cardiac signal. In some embodiments, these artifacts may be due to respiration, cardiac motion, or artifacts induced by applied signal processing, such as filters. Another form of electrical reference catheter can be an internal analog reference electrode, which can act as a low noise “analog ground” for all internal catheter electrodes. Each of these types of reference electrodes can be placed in relatively similar locations, such as near the lower back in an internal vessel (as a catheter) and/or on the lower back (as a patch). In some embodiments, system 100 comprises a reference catheter 58 including a fixation mechanism (e.g. a user activated fixation mechanism), which can be constructed and arranged to reduce displacement (e.g. accidental or otherwise unintended movement) of one or more electrodes of the reference catheter 58. The fixation mechanism can comprise a mechanism selected from the group consisting of: spiral expander; spherical expander; circumferential expander; axially actuated expander; rotationally actuated expander; and combinations of two or more of these.

Referring now to FIG. 4, provided is a block diagram of an embodiment of a cardiac information processing system 400, in accordance with aspects of the inventive concept. The system 400 in FIG. 4 is similar to that of the system 100 in FIG. 1, except in FIG. 4 the catheter includes ultrasound transducers 12 b, here located in the splines of the basket electrode array 12 with the electrodes 12 a. In this embodiment, a single electrode 12 a (e.g., for localization) is paired with an ultrasound transducer 12 b (e.g., for anatomical representation). In one embodiment, there are 48 of such pairs on the electrode array 12. In other embodiments, the system can also localize electrodes not paired with transducers, such as with an AUX catheter and/or a catheter with only electrodes on an array. The catheter 10 also connects to cardiac information console 20 as described in FIG. 1.

With respect to the multiple “pairs” of electrical components, for example, at least one pair comprises an electrode 12 a and an ultrasound transducer 12 b. Each electrode 12 a can be configured to record a voltage (or biopotential), such as the voltage present on a surface of the heart or at a location within a heart chamber HC. Each ultrasound transducer 12 b can be configured to send and/or receive ultrasound signals, such as to produce an anatomical image of the tissue of at least a portion of the heart or other patient anatomical location. When such information is accumulated for multiple pairs 12 a, 12 b over time, an anatomical image of the heart with a superimposed mapping of cardiac activity can be produced for display via US subsystem 27.

In this embodiment, the cardiac information console 20 includes the same biopotential signal path 30 and localization signal path 40 described above with respect to FIG. 1, as well as DFIB protection module 22 and ADC 24. The BIO signal processing module 34 or the LOC signal processing module 44 are also included within cardiac information console 20, as well as UI subsystem 27. The power supply PWR and processor 26 can also be included, including BIO processor 36 and LOC processor 44.

Unlike FIG. 1, an ultrasound (US) signal path 60 is provided, which includes a US isolation MUX 61, US transformer 62, and US generation and detection module 63. The US isolation MUX 61 is connected to the DFIB protection module 22, and is used for turning on/off the US transducers 12 b, such as in a predetermined order or pattern. The US isolation MUX 61 can be a set of high input impedance switches that, when open, isolate the US system and remaining US signal path elements, decoupling the impedance to ground (through the transducers and the US signal path 60) from the input of the LOC and BIO paths. The US isolation MUX 61 also multiplexes one transmit/receive circuit to one or more multiple transducers 12 b on the catheter 10. The US transformer 62 operates in both directions between the US isolation MUX 61 and the US generation and detection module 63. US transformer 62 isolates the patient from the current generated by the US transmit and receive circuitry in module 63 during ultrasound transmission and receiving by the US transducers 12 b. The switches of US transformer 62 selectively engage the transmit and/or receive electronics of module 63 based on the mode of operation of the transducers 12 b, such as to activate one or more of the associated transducers 12 b, such as in a predetermined order or pattern. That is, in a transmit mode, the module 63 receives a control signal from an US processor (within a data processor 26) that activates the US signal generation and connects an output of the transmit amplifier to US transformer 62. The US transformer 62 couples the signal to the US isolation MUX 61 which selectively activates the US transducers 12 b. In a receive mode, the US isolation MUX 61 receives reflection signals from one or more of the transducers 12 b, which are passed to the US transformer 62. The US transformer 62 couples signals into the receive electronics of the US generation and detection module 63, which in-turn transfers reflection data signals to the US processor for processing and use by the user interface system 27 and display 27 a.

In this embodiment, the ADCs and the signal processing are all contained in the cardiac information console 20 for BIO, LOC, and ultrasound. Output to the ADC(s) is a sequence of individual biopotential voltage points for each electrode. As discussed below, these have been filtered and CMRR improved and normalized on a channel-by-channel basis with each channel handled independently. Output to the ADC is also a sequence of localization voltage points for each axis of each patch electrode. And output to the ADC 24 is also a collection of 48 (in this embodiment) reflection distances measured at a single time for ultrasound.

The algorithmic computations are done in the cardiac information console 20, including: process 48 or 80 channels at one time; measure propagation delays between signals; turn x, y, z data into a spatial distribution of location of electrodes; compute and apply corrections to the collection of positions; and/or turn individual distances into a point cloud and manipulate the point cloud.

FIG. 5 is a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, in accordance with aspects of the inventive concept. An IQ demodulator 502 receives outputs from an ADC 24, and analyzes the magnitude and phase of the received signal. In this embodiment, using IQ demodulation provides for maximum noise rejection. Narrowband filter 504 minimizes interference and a time filter 506 prevents intermodulation with ultrasound pulses by enabling selective filtering of signals from any time period. As examples, the time filter 506 can be used for blanking and interleaving signals, e.g., mapping signals, localization signals, and/or ultrasound imaging signals.

A data processor 508 can be configured to perform the computational algorithms applied to global data sets used in localization signal processing.

FIG. 6 is a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, as another implementation of the approach of FIG. 5, in accordance with aspects of the inventive concept.

The embodiment of FIG. 6 shows simultaneous demodulation of multiple frequencies, in a parallel arrangement formed between the ADC 24 and the time filter 506. This embodiment produces highest throughput for localization and allows oversampling to reduce noise. There is an IQ demodulator 502 a, 502 b, 502 c, for each channel coming from the ADC 24. As is shown, there is independent IIR filtering of I and Q components. This approach gives the highest possible signal integrity, with the narrowest band pass possible and the shortest real time delay. The time filter 506 prevents intermodulation with ultrasound pulses.

This approach provides a total synchronous processing chain and allows easy time/state dependent filters.

FIG. 7 is a block diagram of an embodiment of functional elements that cooperate to perform localization signal processing, as another implementation of the approach of FIG. 5, in accordance with aspects of the inventive concept.

The embodiment of FIG. 7 is similar to that of FIG. 6, except there is not a dedicated IIR filter for each I and Q. Instead, there is a time multiplexing of IQ components, using switches, from the IQ demodulators into a multi-channel IIR filter 504. The multi-channel IIR filter 504 includes a sufficient number of channels to accommodate all Is and Qs. In other embodiments, the number of IIR filters 504 can be more than 1 and less than the number of Is and Qs.

This approach reduces computational resources with no additional time delay.

FIG. 8 is an embodiment of a localization method, in accordance with aspects of the inventive concepts. The method 800 of FIG. 8 can be implemented by the various systems described herein.

In step 802, processed I and Q data is received from the signal processing module. In step 804, the IQ data is converted into voltage data. In some embodiments, the voltage data is filtered for abnormal signals and/or outlier data and this data can be excluded from further calculations. In step 806, an axis correction factor is determined and applied, which can be based on a known or measured shape of the electrode array, such as the 48 electrode array 12. There is one axis for each pair of localization electrodes, e.g., reference electrodes 56. For instance, if the shape of the basket is incorrect, one or more axis can be rotated, scaled, and/or deskewed until the basket takes the proper shape, which could be visible on a display of the UI subsystem 27 and manipulatable user mechanisms of the user interface module 27. In step 808, a scaling matrix is determined and applied to the voltage values, again based on the known or measured shape of the electrode array. Here, if the length or size of the array is incorrect, based on the known or determined proportions of the electrode array, one or more of the axes can be scaled (longer or shorter) until the proper size is achieved.

In step 810, position values of the electrodes in the electrode array (e.g., electrode array 12) can be determined, and will have voltage values that are corrected based on steps 806 and 808. In step 812, a fitting algorithm can be performed to fit the calculated electrode positions to the known basket configuration. Additionally, in step 814, additional fitting and rotations can be applied to the calculated electrode positions and the electrode positions on the electrode array can be updated. This fitting step is more precise than the first fitting step, so provides better localization accuracy. In step 816, a next data set is loaded and the method returns to step 804 for further processing.

FIG. 9 is a schematic diagram of an embodiment of an ablation system and an ablation catheter, in accordance with aspects of the inventive concept. There is an ablation system 510 coupled to an ablation catheter 512. An ablation tip 514 is located on a distal end of the ablation catheter 512. The ablation tip 514 delivers ablation energy to the tissue, e.g., RF ablation energy.

In this embodiment, there is no alteration to the “power path”, e.g., no filtering of the power path, so no impedances are added to the chain and no ablation power is wasted in filters. There are filters 520 connected to non-ablation electrodes, e.g., electrodes used as part of a localization system. A high input impedance is maintained for the localization system, which allows localization during delivery of ablation energy. Additionally, in this embodiment, less ablation noise or artifact is coupled into the BIO and/or LOC signals than in the alternate configuration of a filter in the return path between the ablation system 510 and the ground patch 516.

FIG. 10 is a schematic diagram of an embodiment of ultrasound circuitry including an ultrasound high input impedance MUX 61, in accordance with aspects of the inventive concept. The ultrasound high input impedance switch includes ultrasound isolation switches 1010 (single switch shown). Ultrasound isolation switch 1010 connects in front of defibrillation (DFIB) protection module 22 discussed above, and has a separate DFIB protection circuit 1020 which connects to a port to which the localization, mapping, and auxiliary catheters (e.g., an ablation catheter) are connected (See, e.g., connector 20 a FIG. 1).

This approach provides isolation of ultrasound from BIO and LOC signals. It is a minimum capacitance implementation, in which high voltage bias reduces capacitance and a symmetric switch minimizes charge injection. The high voltage also shortens the time for which the switch reaches an “on” state, and minimizes time of distortion for biopotential and localization signals. In one embodiment, OptoFETs isolate the control electronics from DFIB protection circuit 1020.

While the foregoing has described what are considered to be the best mode and/or other preferred embodiments, it is understood that various modifications can be made therein and that the invention or inventions may be implemented in various forms and embodiments, and that they may be applied in numerous applications, only some of which have been described herein. It is intended by the following claims to claim that which is literally described and all equivalents thereto, including all modifications and variations that fall within the scope of each claim. 

1. A localization system, comprising: at least one catheter configured for delivery of one or more biopotential electrodes to a body cavity defined by surrounding tissue; a patient interface module comprising a plurality of localization electrodes configured for fixed orientation relative to the body; and a cardiac information console configured to process both the magnitude and phase of localization signals from the localization electrodes to establish a manipulatable coordinate system for the tissue based on both the magnitude and phase of the localization signals, and to process biopotential signals to orient the biopotential electrodes within the coordinate system. 2.-97. (canceled)
 98. The localization system of claim 1, wherein the cavity is a heart chamber and the surrounding tissue is one or more walls of the heart chamber.
 99. The localization system of claim 1, wherein the biopotential electrodes are disposed on a 3D array.
 100. The localization system of claim 99, wherein the 3D array includes a plurality of splines.
 101. The localization system of claim 99, wherein the 3D array is a basket array, a spiral array, a balloon, radially deployable arms, and/or other expandable and compactible structures.
 102. The localization system of claim 99, wherein the cardiac information console is configured to generate an electronic representation of the 3D array of biopotential electrodes from the biopotential signals.
 103. The localization system of claim 102, wherein the cardiac information console is further configured to rotate the coordinate system to adjust and correct the electronic representation of the 3D array of biopotential electrodes.
 104. The localization system of claim 103, or any other claim, wherein the cardiac information console is further configured to fit the electronic representation of the 3D array of biopotential electrodes to a known or determined geometry of the 3D array of biopotential electrodes.
 105. The localization system of claim 102, further comprising: a user interface system configured to display the electronic representation of the 3D array of biopotential electrodes and the coordinate system.
 106. The localization system of claim 105, wherein the user interface system includes a mechanism that enables a user to rotate and/or scale the coordinate system to graphically adjust and correct an image of the electronic representation of the 3D array of biopotential electrodes.
 107. The localization system of claim 1, wherein the patient interface module includes a patient isolation drive system, a set of patch electrodes, and one or more reference electrodes.
 108. The localization system of claim 107, wherein the localization electrodes include one or more pairs of localization electrodes.
 109. The localization system of claim 108, wherein each pair of localization electrodes defines an axis of the coordinate system.
 110. The localization system of claim 109, wherein the isolation drive system is configured to maintain simultaneous output on all axes generated by the localization electrode pairs.
 111. The localization system of claim 108, wherein the localization electrodes include three pairs of localization electrodes defining axes, each pair of localization electrodes defining one axis of the coordinate system.
 112. The localization system of claim 111, wherein: a first pair of localization electrodes has two patch electrodes placed on opposite sides of the ribs; a second pair of localization electrodes has one patch electrode placed on the lower back and one patch electrode placed on the upper chest; and a third pair of localization electrodes has one patch electrode placed on the upper back and one patch electrode placed on the lower abdomen.
 113. The localization system of claim 111, wherein the axes are non-orthogonal to a natural axis of the body.
 114. The localization system of claim 108, wherein each pair of localization electrodes is driven by a different localization signal.
 115. The localization system of claim 114, wherein each localization signal has a different frequency.
 116. The localization system of claim 1, wherein the cardiac information console further comprises, for each electrode: a biopotential signal path having a high impedance input and configured to receive biopotential signals from the biopotential electrodes; and/or a localization signal path having a high impedance input and configured to receive localization signals from the localization electrodes.
 117. The localization system of claim 116, wherein the cardiac information console further comprises, for each electrode: a DFIB protection circuit coupled between the biopotential signal path and the localization signal path.
 118. The localization system of claim 116, wherein the cardiac information console further comprises: an ADC, for each electrode, coupled to outputs of the biopotential signal path and the localization signal path; an IQ demodulator, for each electrode, coupled to an output of the ADC; a narrow band IIR filter coupled to the IQ demodulator; and a time filter coupled to the IIR filter, and configured to selectively filter out portions of data on a time basis.
 119. The localization system of claim 118, wherein there is one IIR filter, comprising an I portion and a Q portion, for each IQ demodulator.
 120. The localization system of claim 118, wherein there is one multichannel IIR filter for a plurality of IQ demodulators.
 121. The localization system of claim 1, wherein the at least one catheter further includes ultrasound electrodes configured to collect image data to generate one or more images of the tissue.
 122. The localization system of claim 121, wherein the cardiac information console further comprises: an ultrasound signal path having a high impedance input and configured to receive ultrasound signals from the ultrasound electrodes. 